JP2014083232A - Ophthalmologic apparatus, ophthalmology control method, and program - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ophthalmologic apparatus having a function of recognizing whether or not irradiation is performed with a wrong quantity of light (quantity of excessive light) even when measuring light is radiated to a subject's eye, an ophthalmology control method and a program.SOLUTION: An ophthalmologic apparatus includes: a light source for irradiating a subject's eye; an irradiation optical system provided in an optical path between the light source and the eye examined; a first imaging optical system provided with a first optical path diverge member for diverging the optical path of the irradiation optical system and configured to form an image of return light from the eye examined as a first image; and a second imaging optical system provided with a second optical path diverge member for diverging the optical path of the irradiation optical system and configured to form an image of light emitted from the light source not through the eye examined as a second image at a position different from that of the first image.

Description

  The present invention relates to an ophthalmologic apparatus, an ophthalmologic control method, and a program.

  Currently, various standards for medical devices have been established, and it has become necessary for ophthalmic devices that perform examination, measurement, processing, and the like to implement an apparatus using a light amount that can be relieved for the eye to be examined. On the other hand, it is essential to improve the performance of the apparatus in order to make a more accurate diagnosis corresponding to various subjects. For this reason, it is necessary to use a high light quantity laser light source. Therefore, it is necessary to develop an excellent interlock mechanism or the like for ensuring safety.

  As a conventional technique, OCT is performed to open and close a shutter or the like that blocks an optical path based on the amount of reference light (measurement is performed if the amount of reference light is within the allowable range, and measurement is not performed unless the amount of reference light is within the allowable range). An apparatus is known (Patent Document 1).

JP 2011-27715 A

  However, in Patent Document 1, whether or not the measurement light is irradiated on the eye to be examined is switched based on the light amount of the reference light detected in a state where the measurement light is not irradiated on the eye to be examined. According to this, since the light amount of the reference light is not detected when the measurement light is irradiated to the eye to be examined, the laser light flux is prevented from being inappropriate for the eye being examined. There is room for improvement.

  An object of the present invention is to provide an ophthalmologic apparatus, an ophthalmologic control method, and a program having a function capable of recognizing whether or not irradiation is performed with an inappropriate amount of light (excessive amount of light) even when measurement light is irradiated on an eye to be examined. Is to provide.

  In order to achieve the above object, a typical configuration of an ophthalmologic apparatus according to the present invention includes a light source that irradiates an eye to be examined, an irradiation optical system that is provided in an optical path between the light source and the eye to be examined, and the irradiation. A first optical path branching member for branching the optical path of the optical system; a first imaging optical system that forms an image of the return light from the eye to be examined as a first image; and an optical path of the irradiation optical system. Second imaging optics that includes a second optical path branching member that branches, and forms an image of light emitted from the light source not through the eye to be examined at a position different from the first image as a second image. And a system.

  Furthermore, a typical configuration of the ophthalmologic control method according to the present invention includes an irradiation step of irradiating the subject's eye with an irradiation optical system provided in an optical path between the light source and the subject's eye, and the optical path of the irradiation optical system is branched. A first imaging optical system including a first optical path branching member, a first imaging step of forming an image of the light source reflected by the eye to be examined as a first image, and an optical path of the irradiation optical system; A second image forming optical system including a second optical path branching member that branches the image of the light source that does not pass through the eye to be examined is formed as a second image at a position different from the first image. And an imaging step.

  Furthermore, the ophthalmologic control program constitutes another aspect of the present invention.

  According to the present invention, it is possible to recognize whether or not the measurement light is irradiated with an inappropriate light amount (excessive light amount) even when the eye to be examined is irradiated.

(A) is a figure which shows an example of the optical arrangement | positioning of the eye refractive power measuring apparatus which concerns on the 1st Embodiment of this invention, (b) is a functional block diagram. It is a figure which shows an example of arrangement | positioning of the measurement ring image and reference spot image on the image pick-up element which concerns on 1st Embodiment. (A) is a flowchart for explaining an example of the operation according to the first embodiment, (b) is a detailed flowchart of step S4, and (c) shows the number of signals detected at each scanning line position. FIG. It is a figure which shows an example of the optical arrangement | positioning of the refracting power measuring apparatus which concerns on a modification. It is a perspective view of the alignment prism stop which concerns on embodiment of this invention. (A) is explanatory drawing of the state where the alignment of the front-back direction using the alignment prism aperture was suitable, (b) is explanatory drawing of a state too far, (c) is explanatory drawing of a state too close.

  Hereinafter, an example of an embodiment of the present invention will be described with reference to the drawings.

<< First Embodiment >>
Fig.1 (a) shows an example of the optical arrangement | positioning of the eye refractive power measuring apparatus which concerns on the 1st Embodiment of this invention.

(Fixed target projection optical system and alignment light receiving optical system)
First, in the reflection direction of the dichroic mirror 107, a fixation target projection optical system and an alignment light receiving optical system that shares anterior eye portion observation and alignment detection of the eye to be examined are arranged. On the optical path 05 of the fixation target projection optical system, a lens 114, a dichroic mirror 212, a lens 119, a folding mirror 120, a lens 121, a fixation target 122, and a fixation target illumination light source 124 are sequentially arranged.

  At the time of fixation fixation, the projected luminous flux of the light source 124 for illuminating the fixation target illuminates the fixation target 122 from the back side, and the fundus of the eye E to be examined through the lens 121, the folding mirror 120, the lens 119, and the lens 114. Projected to Er. The lens 121 can be moved in the optical axis direction by a fixation guidance motor 123 in order to guide the diopter of the eye E and realize a cloudy state.

  In addition, an alignment prism diaphragm 223, a lens 116, a diaphragm 117, and an image sensor 118 are sequentially arranged on the optical path 04 in the reflection direction of the dichroic mirror 212, so that the anterior eye portion of the eye to be examined and alignment detection can be performed. . Here, the alignment prism aperture 223 is driven by an alignment prism aperture drive solenoid (not shown), and the aperture 117 is driven by an aperture drive solenoid (not shown).

  By inserting / extracting the alignment prism diaphragm 223, alignment can be performed when the alignment prism diaphragm 223 is on the optical path 06, and anterior eye observation or transillumination observation can be performed when retracted from the optical path.

  As shown in FIG. 5, the alignment prism diaphragm 223 is provided with three openings (a central part 223a and left and right ends 223b and 223c) in a disc-shaped diaphragm plate. In addition, alignment prisms 301a and 301b that transmit only a light beam having a wavelength of about 880 nm, for example, are attached to the dichroic mirror 212 side of the openings 223b and 223c at both ends in the left-right direction.

  Further, anterior eye part illumination light sources 125a and 125b having a wavelength of, for example, about 780 nm are disposed obliquely in front of the anterior eye part of the eye E to be examined. The light flux from the anterior ocular segment illuminated by the anterior ocular illumination light sources 125 a and 125 b is received by the image sensor 220 via the dichroic mirror 107, the lens 114, the dichroic mirror 212, and the central opening 223 a of the alignment prism diaphragm 223. An image is formed on the sensor surface. Here, the central opening 223a of the alignment prism diaphragm 223 is configured to allow a light beam having a wavelength of 780 nm or more of the anterior segment illumination light sources 221a and 221b to pass.

(alignment)
The light source for alignment detection is also used as the measurement light source 101 for measuring eye refractive power. At the time of alignment, the translucent diffusion plate 105 is inserted into the optical path by the diffusion plate driving solenoid. The position where the diffusion plate 105 is inserted is a primary image formation position by the projection lens 102 of the measurement light source 101 and is inserted at the focal position of the lens 106. As a result, the image of the measurement light source 101 is once formed on the diffusion plate 105, which becomes a secondary light source and is projected from the lens 106 toward the eye E as a thick parallel light beam.

  This parallel light beam is reflected by the eye cornea Ef to be examined to form a bright spot image. Then, a part of the light beam is again reflected by the dichroic mirror 107, further reflected by the dichroic mirror 212 through the lens 114, transmitted through the alignment prism diaphragm 223, converged by the lens 116, and imaged on the image sensor 118. The

  That is, the light beams divided by the openings 223a, 223b, and 223c of the alignment prism diaphragm 223 and the prisms 301a and 301b are formed on the image sensor 220 as index images Ta, Tb, and Tc. In addition, the bright spot images 221a 'and 221b' of the external illumination light sources 221a and 221b are imaged by the imaging element 220 together with the anterior eye segment illuminated by the external illumination light sources 221a and 221b.

  As shown in FIG. 6A, the alignment is completed in a state where the three corneal bright points Ta, Tb, and Tc are arranged in a line in a direction orthogonal to the horizontal direction. When the alignment in the Z direction (front-rear direction) is poor, FIG. 6B shows a case where it is too far, and FIG. 6C shows a case where it is too close.

(Refractive power measurement)
The optical system related to the optical path 01 is for measuring eye refractive power. The light beam emitted from the measurement light source 101 is primarily focused in front of the lens 106 by the lens 102 while being focused by the aperture 103 and passes through the lens 106 and the dichroic mirror 107 to reach the center of the pupil of the eye E to be examined. Lighted. The luminous flux forms an image on the fundus Er, and the reflected light enters the lens 106 again through the center of the pupil. The incident light beam is transmitted through the lens 106 and then reflected around the perforated mirror 104 (functioning as a first optical path branching member that branches the optical path 01 of the irradiation optical system that irradiates the eye to be examined).

  The reflected light beam is separated by the first imaging optical system including the lenses 106 and 111 by a ring-shaped diaphragm 109 conjugate with the eye pupil Ep to be examined, via a prism 110 that displaces the light beam in each meridian direction. A ring image is formed on the light receiving surface of the image sensor 112. If the eye E is a normal eye, the ring image is a predetermined circle, and the curvature of the circle is small for the myopic eye, and the curvature of the circle is large for the hyperopic eye. When the subject eye E has astigmatism, the ring image becomes an ellipse, and the angle formed by the horizontal axis and the major axis of the ellipse becomes the astigmatism axis angle. The refractive power is obtained based on the coefficient of the ellipse. The examiner can visually recognize the image picked up by the image pickup device 112 on the monitor 200.

(Reference light for laser irradiation judgment)
Here, as an example, the measurement light source 101 for measuring eye refractive power uses an SLD (Super Luminescent Diode) that generates laser light having a wavelength of 880 nm, which is near infrared light. The measurement light source 101 is also used as a reference light source for laser irradiation determination described below.

  The optical path 02 along which the light reflected by the light splitting mirror 126 as the second optical path branching member that branches the optical path 01 of the irradiation optical system that irradiates the eye to be examined travels a part of the projection light projected from the laser light source 101. This is an optical path for monitoring as reference light via the optical path 02. That is, the laser beam emitted from the measurement light source 101 is coupled to the image sensor 210 as a spot image by the second imaging optical system including the lens 102, the diaphragm 103, the light dividing mirror 126, the mirror 127, and the light dividing mirror 128. Imaged.

  On the other hand, the measurement light is reflected by the eye E, and then is pupil-separated by the ring-shaped stop 109 and formed as a ring image on the light receiving surface of the image sensor 112 via the prism 110 and the lens 111. Since the measurement light becomes a ring-shaped light beam and the reference light becomes a spot-shaped light beam, the position where the reference light enters the optical path 03 (that is, the position of the light splitting mirror 128) is closer to the image sensor 112 than the stop 109. There must be.

  FIG. 2 shows a positional relationship between the ring image of the measurement light and the spot image of the reference light formed inside the image sensor 112 according to the present embodiment. Reference numeral 301 denotes an effective pixel surface of the image sensor 112. Reference numeral 302a denotes a ring image having the most diopter of the eye to be examined, and 302b denotes a ring image having the most diopter of the eye to be examined. Therefore, the region closer to the center than the ring image 302b is a region that is not used for measurement. Reference numeral 303 denotes a spot image by reference light, which is positioned near the center so as not to overlap the ring image 302b.

  On the two-dimensional surface of the image sensor 112, it is set in which region the most positive ring image and the most negative ring image of the diopter are captured in the measurable range of eye refractive power. Yes. That is, a region that is not used for detecting a ring image on the two-dimensional surface of the image sensor 112 is known in advance. By forming a spot image of the reference light in that region, the state of the laser light source can be monitored by the reference light even during measurement of the ring image. Note that the positional relationship between the ring image and the spot image is not limited to that shown in FIG. 3, and the positional relationship shown in FIG. 3 is not necessary as long as the ring image and the spot image do not overlap.

(Difference in amount of received light between measurement light and reference light)
Here, the measurement light and the reference light are light beams emitted from the same laser light source, but since the optical paths to the image sensor 112 are different, the amounts of received light on the image sensor are different. In order to simultaneously measure the measurement light and the reference light, it is desirable to make the measurement gains the same in the image sensor, and it is desirable to suppress the difference in the amount of received light between the measurement light and the reference light. By making the measurement gain the same, it is possible to measure the reference beam and the measurement beam without adjusting the gain during measurement, and the same noise level can reduce the measurement error between the reference beam and the measurement beam. It becomes possible.

  Note that the terms “simultaneous” and “same” in the present invention are not a concept including only the case of exactly the same or the same, but a concept including a case of substantially the same or substantially the same.

  In FIG. 1A, the attenuation factor of the measurement light is determined from the dichroic mirror 107 to the light splitting mirror 128 in the optical path 03 through the holed mirror 104. Here, the transmittance of the dichroic mirror 107 is 90%, the reflectance of incident light reflected by the fundus of the eye to be examined is 0.1%, the transmittance of the dichroic mirror 107 through which the light beam passes again is 90%, and there is a hole. It is assumed that there is no loss due to the reflection of the mirror 104. Also, assuming that the transmittance of the prism 110 in the optical path 03 reflected by the perforated mirror 104 is 90%, the attenuation factor of the measurement light is about 0.15%.

  On the other hand, the attenuation factor of the reference light is determined between the light dividing mirror 126 and the light dividing mirror 128 in the optical path 02. Since the attenuation rate of the measurement light is about 0.15%, if the attenuation rate of 0.15% is supplemented only by the light splitting mirror 126, the transmittance to the optical path 01 is about 99.85%, and the optical path 02 The reflection may be about 0.15%.

  On the other hand, when an optical member is added on the optical path 02 and the received light amount of the reference light is set, it is previously set between the light dividing mirror 126 and the mirror 127 or between the mirror 127 and the light dividing mirror 128. Insert an optical filter with a determined transmittance. For example, when the transmission and reflection by the light splitting mirror 126 are 50 to 50, the measurement light is 50 × 0.15% = 0.075, so the reference light is in the vicinity of 0.075 of the measurement light. Therefore, an optical filter having a transmittance of about 0.15% may be inserted.

  Thereby, the received light quantity of the reference light can be set. Here, the transmittance of the optical filter to be inserted is determined based on the attenuation factor of the measurement light so that the measurement light and the reference light have the same light quantity.

  Further, when the received light amount of the reference light is set by the reflectance and transmittance of the light splitting mirrors 126 and 128 and the mirror 127 constituting the optical path 02, the transmittance of the light splitting mirror 126, the light splitting mirror 128, and the mirror 127 are set. Change the reflectance. Thereby, the received light quantity of the reference light can be set. Here, the transmittance and reflectance of the mirror are determined based on the attenuation rate of the measurement light so that the measurement light and the reference light have the same light quantity.

(Laser irradiation switching and light source light quantity adjustment)
The irradiation switching of the laser light beam to the eye to be examined by the shutter 108 that switches the state in which the light from the light source is restricted to the eye to be examined and the state in which the light from the light source to the eye to be examined is not restricted is as follows. To be implemented. First, in a state immediately after the start of measurement, the shutter 108 is shielded from light so that the laser beam is not irradiated on the eye to be examined.

  Since the optical path 01 is blocked by the shutter 108, the measurement light does not return to the optical path 03. On the other hand, the reference light passes from the light source 101 through the lens 102 and the diaphragm 103, is reflected by the light splitting mirror 126, enters the optical path 02, is reflected by the mirror 127, and the light splitting mirror 128, and is reflected on the effective pixel surface 301 of the image sensor 112. The ring image is formed in the vicinity of the center, which is an unused area.

  The CPU 113 compares the output value of the spot image formed near the center with a predetermined value set in advance. When the output value is equal to or smaller than the predetermined value (when it is within the allowable range), the CPU 113 controls the drive circuit (not shown) of the shutter 108 to open the optical path 01. That is, the state is switched to a state in which the laser beam is irradiated to the eye to be examined. Here, the predetermined value is, for example, the maximum value that does not adversely affect the eye to be examined. On the other hand, when the output value exceeds the predetermined value (when it is not within the allowable range), the CPU 113 maintains the state where the optical path 01 is blocked and adjusts the laser light source light amount so as not to exceed the predetermined value.

  The above description relates to the state before the measurement in which the laser beam is applied to the eye to be examined, but the CPU 113 compares the output value with a predetermined value even during the measurement in which the laser beam is applied to the eye to be examined. doing. When the output value exceeds a predetermined value (when it is not within the allowable range), the CPU 113 immediately controls the drive circuit (not shown) of the shutter 108 to block the optical path 01 and adjust the laser light source light amount. . The adjustment of the laser light source light amount by the CPU 113 as the light amount control means is performed by controlling the current and voltage of the laser light source. As a result, the light amount of the laser light source is reduced, and the output value becomes a predetermined value or less (within an allowable range).

  When the output value becomes equal to or less than a predetermined value (within an allowable range), the CPU 113 controls the driving circuit (not shown) of the shutter 108 to open the optical path 01 so that the eye can be irradiated with the laser beam. .

  However, if the output value does not fall below the predetermined value (within the allowable range) even when the laser light source quantity is controlled, there is a possibility that the device is broken, and thus a warning or the like is displayed on the monitor 200. When the warning is displayed, the examiner can surely recognize the abnormality.

(flowchart)
(Flow chart of the entire device)
The above configuration will be described along with the block diagram shown in FIG. 1B along the flowchart shown in FIG. 3A. Here, the CPU 113 in FIG. 1B controls the laser light source 101, the shutter 108, the monitor 200 and the like as a whole.

  When the measurement is started (S1 in FIG. 3A), confirmation (S2 in FIG. 3A) is performed to block the laser beam and prevent the laser beam from being emitted outside the apparatus. Next, the step of generating laser light (S3 in FIG. 3A) proceeds, the laser light source (also serving as the measurement light source) 201 is turned on, and the output of the laser light is measured (S4 in FIG. 3A). ), The laser output is measured by the image sensor 112 as an output measuring means.

  Next, a conversion step (S5 in FIG. 3A) for conversion based on a conversion formula between the laser output, the output of the laser light stored in the storage means (not shown), and the dose irradiated to the fundus of the eye to be examined. ), The amount of irradiation irradiated to the eye fundus of the subject is converted. In other words, the amount of light incident on the eye to be examined is determined.

  Then, based on the determination of the amount of the converted dose, if it is equal to or less than a predetermined value, the CPU 113 switches the shutter 108 and switches from shutter closing to shutter opening (S6 and S7 in FIG. 3A). Then, after performing the above-described auto-alignment in S8 of FIG. 3A, measurement with a laser beam is performed in S9 of FIG.

  That is, a first imaging optical system including an irradiation step of irradiating the subject's eye with an irradiation optical system provided in an optical path between the light source and the eye to be examined, and a first optical path branching member that branches the optical path of the irradiation optical system. Thus, the first imaging step for forming an image of the light source reflected by the eye to be examined as a first image is started. On the other hand, regarding the measurement of the laser output (S4 to S6, S9 to S10), the second imaging optical system including the second optical path branching member that branches the optical path of the irradiation optical system is used for the light source that does not pass through the eye to be examined. There is a second imaging step in which the image is imaged as a second image at a position different from the first image.

  When the converted irradiation amount is larger than the predetermined value, the CPU 113 as the light amount adjusting means adjusts the light amount in the light amount adjusting step for adjusting the laser light (S12 in FIG. 3A). In S13 of the light amount adjustment step, the CPU 113 determines whether or not the adjustment is effective by determining whether or not the value of the laser light amount has changed. When the light amount adjustment is effective, the process returns to S4 in FIG.

  If the light amount adjustment is not effective, a visual warning display is given to the monitor 200 as a means for notifying the uncontrollable state in S14 of FIG. The state in which the warning is displayed in this way is, for example, an abnormality or failure of the apparatus such as a state in which the output control of the laser light source cannot be performed or an optical member is damaged and an abnormal output value is detected. Applicable state.

  When performing measurement with laser light in S9 of FIG. 3 (a), it is possible to simultaneously confirm the laser output and convert the laser irradiation amount, so in S10 of FIG. 3 (a), it is determined whether or not the laser irradiation amount is a predetermined value or less. To do. If it is equal to or smaller than the predetermined value, the process proceeds to S15, where it is determined whether an appropriate measurement value is obtained and the measurement can be completed, and if it is satisfactory, the measurement is completed (S16). If the laser irradiation amount is not less than the predetermined value in S10 of FIG. 3A, the shutter 108 is closed to block the optical path 01 (S11), and the process proceeds to S12 to adjust the laser light source light amount. If the measurement cannot be completed because an appropriate measurement value cannot be obtained in S15 of FIG. 3A, the process returns to S8, the position is adjusted again, and the measurement is performed again.

  Here, when performing measurement with laser light, it is possible to simultaneously confirm the laser output and convert the laser irradiation amount. FIG. 3B shows the signal detection in FIG. 3B as a detailed flow of S10 in FIG. Shown with c). When an optical image in the image sensor 112 is sequentially detected by each scanning line (S10a), it is determined whether or not there is three scanning lines in one scanning line (S10b). Sc is extracted (S10d), and the intensity of the middle signal Sc is output (S10e). If No, the position is changed from the m-th scanning line to the (m + 1) -th scanning line (S10c), and the process is repeated until one scanning line has three scanning lines.

  As described above, in the present embodiment, the output of the reference light can be monitored even during measurement, and measurement can be performed while confirming that the output value is within the allowable range. In addition, when the output value becomes an abnormal value (when it is not within the allowable range), it is possible to cut off the optical path and adjust the light source light amount to decrease. Thereby, it is ensured that a laser beam that does not become inappropriate is irradiated to the eye to be examined.

(Modification 1)
In the above-described embodiment, the same imaging device 112 that captures the measurement ring image and the reference spot image is used as a measurement spot image. It is displaced to. However, the present invention is not limited to this, and as shown in FIG. 4, the measurement ring image and the reference spot image are separately captured by different imaging elements 112 and 112 a, and the position of the measurement ring image and the reference spot are determined. You may make it not overlap with the position of an image. In FIG. 4, the reference spot image is formed on the image sensor 112a by the light beams reflected by the light splitting mirror 126 and the mirrors 127a and 127b.

(Modification 2)
In the above-described embodiment, the image of the light source (first image) reflected by the eye to be examined is originally formed at the center position of the image sensor, and a ring image is formed as an image displaced in each meridian direction by the action of the prism 110. It was explained that the position of the reference spot image does not overlap. However, the present invention is not limited to this. For example, an image of the light source (first image) reflected by the subject's eye cornea is formed at the center position of the image sensor, while an image of the light source that does not pass through the subject's eye is displayed as the second image. A displacement member may be provided in the reference optical path so as to form an image at a position deviating from the center position of the same image sensor.

  Specifically, the reference spot image can be formed at a position deviating from the center of the image sensor 113 by rotating and displacing the mirror 127 within the paper surface.

(Modification 3)
In the above-described embodiment, when the output of the reference light exceeds the allowable range, the optical path of the irradiation optical system that irradiates the eye to be examined is switched to the cutoff state by the shutter 108, but the present invention is not limited to this. That is, when the light amount adjustment of the light source is not performed, the light source 101 may be switched to the off state without using the shutter 108.

(Other embodiments)
The present invention is also realized by executing the following processing as an ophthalmologic control program for causing a computer to execute each step of the ophthalmologic control method. That is, software (program) that realizes the functions of the above-described embodiments is supplied to a system or apparatus via a network or various storage media, and a computer (or CPU, MPU, or the like) of the system or apparatus reads the program. It is a process to be executed.

101..Measurement light source, 102..Lens, 104..Perforated mirror, 108..Shutter, 109..Ring diaphragm, 110: Prism, 111..Lens, 112..Image sensor, 126, 128 .. Light splitting mirror, 200 ... monitor, E ... eye to be examined

Claims (9)

A light source for irradiating the eye to be examined;
An irradiation optical system provided in an optical path between the light source and the eye to be examined;
A first imaging optical system that includes a first optical path branching member that branches the optical path of the irradiation optical system, and that forms an image of return light from the eye as a first image;
A second optical path branching member that branches the optical path of the irradiation optical system is provided, and an image of light emitted from the light source not passing through the eye to be examined is formed as a second image at a position different from the first image. A second imaging optical system that
An ophthalmologic apparatus comprising:   The ophthalmologic apparatus according to claim 1, wherein the first image and the second image are formed on the same image sensor.   The ophthalmologic apparatus according to claim 2, wherein the first image is a ring image, and the second image is a spot image.   The ophthalmologic apparatus according to claim 3, wherein the spot image is formed inside the ring image.   The apparatus according to claim 1, further comprising: a switching unit configured to switch the light source from the light source to the eye to be inspected in a state where the output of the second image exceeds an allowable range, or to switch the light source off. The ophthalmologic apparatus according to any one of 1 to 4.   2. The apparatus according to claim 1, further comprising: a light amount control unit configured to control the light amount of the light source to be reduced based on the output of the second image when the output of the second image exceeds an allowable range. The ophthalmologic apparatus according to any one of 5.   The first image and the second image of the optical member constituting the first imaging optical system or the second imaging optical system so that the amount of light received by the imaging element is equal. The ophthalmologic apparatus according to any one of claims 2 to 6, wherein a reflectance or a transmittance is set. An irradiation step of irradiating the subject's eye with an irradiation optical system provided in an optical path between the light source and the subject's eye;
A first image forming optical system including a first optical path branching member that branches an optical path of the irradiation optical system, and forms an image of the light source reflected by the eye to be examined as a first image. Steps,
In a second imaging optical system comprising a second optical path branching member that branches the optical path of the irradiation optical system, a position different from the first image with the image of the light source not passing through the eye to be examined as a second image A second imaging step for imaging on
An ophthalmologic control method comprising:   An ophthalmologic control program for causing a computer to execute each step of the ophthalmologic control method according to claim 8.